Implantation of a transapical ventricular assist device and kit for same

ABSTRACT

A method of implanting a blood pump in a heart of a mammalian subject includes maintaining a temporary plug in an inlet opening of a pump having a pump body and an outlet cannula projecting from the pump body, advancing the pump into a ventricle of the heart through a hole in a wall of the heart so that the inlet of the pump is disposed within the ventricle and the outlet cannula extends through a valve of the heart into an artery, and then withdrawing the temporary plug from the inlet of the pump.

CROSS-REFERENCE TO RELATED APPLICATION

This application is a divisional of U.S. patent application Ser. No.14/799,703 (now U.S. Pat. No. 9,656,011), filed Jul. 15, 2015, entitledIMPLANTATION OF A TRANSAPICAL VENTRICULAR ASSIST DEVICE AND KIT FORSAME, and claims priority to U.S. Provisional Application Ser. No.62/025,119, filed Jul. 16, 2014, the entirety of which is incorporatedherein by reference.

TECHNICAL FIELD

The present invention relates to a blood pump, and, more particularly,relates to a system and method for facilitating implantation of a bloodpump.

BACKGROUND

In certain disease states, the heart lacks sufficient pumping capacityto meet the needs of the body. This inadequacy can be alleviated byproviding a mechanical pumping device referred to as a ventricularassist device (“VAD”) to supplement the pumping action of the heart.Considerable effort has been devoted to providing a VAD which can beimplanted and which can remain in operation for months or years to keepthe patient alive while the heart heals (bridge-to-recovery), or whichcan remain in operation permanently (destination therapy) or until asuitable donor heart becomes available if the heart does not heal(bridge-to-transplantation).

The VAD is typically connected to the heart, most commonly to the leftventricle, which is responsible for pumping oxygenated blood through theaortic valve to the general body. For example, a VAD may include a pumpwhich is installed in the body outside of the heart. The VAD may have aninlet cannula connected to the interior of the left ventricle andconnected to the intake of the pump. The VAD may also include an outlettube connected to the outlet of the pump, routed along the outside ofthe heart, and grafted to the aorta. Installation of a VAD, particularlya VAD that makes use of an outflow graft, often requires cardioplegiaand/or a cardiopulmonary bypass (“CPB”). Cardioplegia and CPB can extendthe time of the implantation procedure and has risks which can besignificant.

As disclosed in commonly owned U.S. Publication No. 2009/0203957, thedisclosure of which is hereby incorporated by reference herein, onesolution developed to avoid the need for an outflow graft is a pump thatis implantable within the left ventricle, which can pump blood disposedwithin the left ventricle directly through the aortic valve via anoutflow cannula coupled to an outlet of the pump. Installation of such adevice is typically performed by inserting the outflow cannula and pumpthrough a cored opening in the apex of the heart. This device avoids theneed for connecting an outflow cannula external to the heart, andgreatly simplifies the installation procedure.

Despite the considerable efforts devoted to improvements in VADs, stillfurther improvement would be desirable.

SUMMARY

Described herein are systems/kits, methods, and devices that facilitateimplantation of a VAD within one or more chambers of the heart. Inparticular, one aspect of the present disclosure describes a transapicalVAD that includes an axial flow pump and a pedestal. Also described is acatheter utilized in conjunction with the implantation of the VAD. Thecatheter desirably includes at least two lumens one of which operates aballoon and the other of which communicates with a distal end of thecatheter and is capable of removing air or other fluid disposed beyondor distal to the balloon. The catheter can also include a transducer,such as a pressure transducer, capable of measuring pressure of a fluidbeyond or distal to the balloon.

Also described are methods of implantation, which generally includegaining access to the apex of the heart, attaching a mounting ring tothe apex, coring the apex through the mounting ring, partially insertingthe VAD into the heart through the cored opening, de-airing the VAD viaa catheter, continuing advancement of the VAD into the heart, measuringa physical condition within the heart, such as pressure, affixing theVAD to the heart, removing the catheter, and plugging the VAD.

Thus, in one aspect of the present disclosure, a method of implanting ablood pump in a heart of a mammalian subject includes maintaining atemporary plug in an inlet opening of a pump having a pump body and anoutlet cannula projecting from the pump body. The method desirably alsoincludes advancing the pump into a ventricle of the heart through a holein a wall of the heart so that the inlet of the pump is disposed withinthe ventricle and the outlet cannula extends through a valve of theheart into an artery, and withdrawing the temporary plug from the inletof the pump.

Additionally, the method may include mounting a ring to the wall of theheart and forming the hole in the wall of the heart within the ring.Also, the step of advancing the pump may include advancing a pedestalmechanically connected to the pump into the hole and into the ring, andsecuring the pedestal to the ring. The temporary plug may be mounted onan elongated catheter and the catheter may extend through a channel inthe pedestal when the pump is advanced into the ventricle. Further, thestep of withdrawing the temporary plug may include withdrawing thecatheter and the plug through the channel in the pedestal and thenclosing the channel.

Continuing with this aspect, the step of maintaining the temporary plugmay include maintaining the temporary plug in an expanded condition, andthe step of removing the plug may include collapsing the plug. The plugmay include a balloon. Also, the step of maintaining the temporary plugin an expanded condition may include maintaining the balloon in aninflated condition, and the step of collapsing the temporary plug mayinclude deflating the balloon.

The method may also include purging the pump and the outlet cannula ofair by allowing air to escape from the pump and the outlet cannulathrough the catheter while the outlet cannula is at least partiallypositioned within the heart or artery. Further, the method may includemeasuring pressure in the heart or artery using a pressure measurementinstrument communicating with the interior of the pump through thecatheter.

The ventricle may be the left ventricle and the valve may be the aorticvalve. In addition, the steps of the method may be performed withoutcardiopulmonary bypass or cardioplegia.

In another aspect of the present disclosure, a pump installation kitcomprises a pump including a pump body having an interior and an inletcommunicating with the interior, a pumping element mounted within theinterior, and an outlet cannula communicating with the interior of thepump body. The pump is desirably adapted for mounting with the pump bodyand inlet disposed within a ventricle of a heart. The kit preferablyincludes a temporary plug which is adapted for releasable, sealingengagement in the inlet.

Additionally, the kit may include a securement/mounting ring adapted formounting to the outside of the heart, and a pedestal adapted formounting to the securement ring. The pedestal may be mechanicallycoupled to the pump. When the pedestal is mounted to the securementring, the pedestal may have a channel having proximal and distal ends.The distal end of the channel may communicate with the ventricle, andthe proximal end of the channel may be disposed outside of the heart.

Continuing with this aspect, the kit may include an elongated elementmechanically connected to the temporary plug. The elongated element mayextend through the channel when the temporary plug is engaged in theinlet. The temporary plug may be adapted to pass out of the heartthrough the channel after the temporary plug is disengaged from theinlet port. The temporary plug may have an expanded condition and acollapsed condition, and the temporary plug may be adapted to pass outthrough the channel in the collapsed condition. The elongated elementmay be a catheter having an inflation lumen, and the temporary plug mayinclude a balloon communicating with the inflation lumen. Also, theelongated element may be a catheter having a fluid lumen. The fluidlumen may communicate with the interior of the pump when the temporaryplug is engaged in the inlet port. A pressure measuring instrument maybe connectable to the fluid lumen

Furthermore, the kit may include a closure adapted to seal the channelin the pedestal. The closure may include a screw adapted to threadedlyengage the channel. A resilient seal may be disposed within the channel.The resilient seal may sealingly engage the elongated element and thepedestal when the elongated element is disposed within the channel. Theresilient seal may be a one-way valve adapted to prevent blood flow fromthe proximal end of the channel when the elongate element is removedtherefrom.

BRIEF DESCRIPTION OF THE DRAWINGS

The features, aspects, and advantages of the present invention willbecome better understood with regard to the following description,appended claims, and accompanying drawings in which:

FIG. 1 is an elevational view of a transapical VAD implantation kitincluding a ventricular assist device and a catheter according to oneembodiment of the present disclosure.

FIG. 2 is a partially sectional view depicting elements of the kit ofFIG. 1.

FIGS. 3-8 are perspective views depicting steps in a method ofimplantation using the kit of FIG. 1.

FIG. 9 is a partially transparent perspective view of another embodimentof a transapical VAD implantation kit.

DETAILED DESCRIPTION

As used herein, when referring to the disclosed devices, the term“proximal” means closer to the operator or in a direction toward theoperator and the term “distal” means more distant from the operator orin a direction away from the operator. Also, as used herein, the terms“about,” “generally,” and “substantially” are intended to mean thatslight deviations from absolute are included within the scope of theterm so modified.

FIG. 1 depicts a transapical VAD installation kit 10 according to oneembodiment of the present disclosure. Installation kit 10 generallyincludes a transapical VAD and a catheter 50. The transapical VADdelivers blood flow in line with the native heart and eliminates theneed for CPB, cardioplegia, or an outflow graft to the aorta orpulmonary artery. The transapical VAD is generally comprised of a pump12 and a pedestal 40 mechanically coupled to pump 12 via an elongatemember 14.

Pump 12 may be generally as shown in the '957 Publication. It includes apump body 30. Pump body 30 includes a tubular housing 37 defining aninlet port 34 at a proximal end of pump body 30 and an outlet port 35 ata distal end of pump body 30. A rotor 36 or axial flow impeller having aplurality of blades projecting outwardly therefrom is rotatably disposedwithin tubular housing 37. Rotor 36 may be formed from a unitary pieceof magnetizable, biocompatible material, such as biocompatibleplatinum-cobalt or platinum-cobalt-boron alloy. Rotor 36 may bemagnetically or hydrodynamically levitated within housing 37. Duringoperation, rotor 36 is rotatable about an axis thereof by a motor stator38 that is disposed about tubular housing 37 in order to urge fluid frominlet port 34 to outlet port 35. Motor stator 38 is configured toprovide a rotating magnetic field and preferably contains magneticlaminations and wire coils. An exterior shroud 32 surrounds housing 37and motor stator 38. Shroud 32 may be formed from any biocompatiblematerial including, but not limited to, titanium, ceramic or polymer.Additionally, shroud 32 may be coated by a thromboresistant coating orother hemodynamically suitable coating.

Pump 12 also includes an outflow cannula 20 extending distally fromoutlet port 35 of pump body 30. Cannula 20 may be made from anybiocompatible material including, but not limited to, metallic and/orpolymeric materials, such as thermoplastic polyurethanes, silicone,polycarbonate-urethanes, polyether-urethanes, aliphatic polycarbonate,titanium, barium sulfate, and any combinations thereof. Additionally,cannula 20 may include radiopaque materials incorporated into itsstructure at particular locations along the length of cannula 20 toallow for radiographic determination of the cannula's positioningrelative to the patient's anatomy. For example, as shown in FIG. 2,cannula 20 may include a radiopaque bead 26, such as a titanium orplatinum bead, embedded within its structure at a distal end thereof,which may help with fluoroscopic visualization.

Outflow cannula 20 may be straight or bent and is generally a hollow,elongate structure that is dimensioned for partial placement into anaorta or pulmonary artery while pump body 30 is positioned in the leftor right ventricles, respectively. A cross-sectional dimension ofoutflow cannula 20 may taper from pump body 30 such that thecross-sectional dimension near pump body 30 is larger relative to thecross-sectional dimension farther from pump body 30. For example,cannula 20 may have a larger diameter near pump body 30 and a smallerdiameter at a distal end of cannula 20.

The distal end of cannula 20 is defined by a distal tip 24 that includesone or more outflow openings 22 communicating with the interior of pumpbody 30. Outflow cannula 20 preferably also may include internal vanes(not shown), which convert rotational momentum of blood leaving rotor 36into useful pressure. In some embodiments, the vanes may be locatedproximal to distal tip 24 or may be included in pump body 30 downstreamof or distal to rotor 36.

Pedestal 40 is generally a cylindrical member having a proximal todistal axis (not shown). Exemplary pedestals and methods of implantationcan be found in U.S. Patent Application Publication 2015/0038770, thedisclosure of which is hereby incorporated herein by reference in itsentirety. Pedestal 40 includes an electrical connection 16 that iscoupled to a power source and/or controller disposed outside of theheart. Electrical connection may enter into a proximal end of pedestal40 in a transverse direction with respect to the proximal to distal axisof pedestal 40. Electrical connection 16 may be rerouted within pedestal40 so that electrical connection 16 extends in a generally axialdirection along the longitudinal axis of pedestal 40 and throughelongate member 14 into pump body 30 where it is electrically coupled tomotor stator 38.

A channel 42 may extend into a proximal end of pedestal 40 and exitthrough a distal end thereof. Channel 42 preferably has a diameterdimensioned to receive an elongate catheter therein. Additionally,pedestal 40 may be positioned respective to pump 12 such that channel 42is coaxial with a bore of pump housing 37. A resilient seal 44 may bedisposed within channel 42 to serve as a temporary seal of channel 42.For example, resilient seal 44 may be a one-way valve press-fit intochannel 42. Resilient seal 44 may be configured to prohibit blood frompassing proximally within channel 42. For example, resilient seal 44 mayhave leaflets that open in one direction. In addition, resilient seal 44may be configured to allow catheter 50 to be passed through channel 42in a proximal to distal direction and removed therefrom in the oppositedirection, as described further below. In addition, resilient seal 44may be configured to engage catheter 50 when disposed within channel 42and to provide a seal around catheter 50. For example, resilient seal 42may be made from a flexible yet resilient biocompatible material thatbiases toward a closed or contracted condition. In addition, channel maynarrow 42 at a location distal to resilient seal 44 so as to preventresilient seal 44 from being dislodged from pedestal 40 in a distaldirection. In another embodiment, seal 44 may contract around catheter50 to provide a temporary seal while catheter is disposed within channel42 but may not seal channel 42 when catheter 50 is removed therefrom.

Channel 42 may be internally threaded at or near the proximal end ofpedestal 40. Such threading may correspond to threading of a removableclosure 46 (see FIG. 8), such as a screw. However, alternativeengagement features other than threading are contemplated, such as aMorse taper, for example. As discussed below, removable closure 46sealingly engages pedestal 40 within channel 42 after removal of thecatheter to permanently seal or plug the proximal end of pedestal 40 andprovide redundancy to resilient seal 44.

Pedestal 40 may serve as an intermediary between an external powersupply and/or controller and pump body 30. In addition, pedestal 40 mayserve as a support structure for attachment to a ventricular wall of theheart. Pedestal 40 may be made from any biocompatible material includingtitanium, ceramic or polymer. In addition, pedestal 40 may include asintered coating on an outer surface thereof to promote tissueingrowth/attachment. The outer surface may also have engagement features(not shown) for engaging sutures attached to a mounting ring to helpfurther secure pedestal to a ventricular wall.

Catheter 50 is generally an elongate structure that includes a pluralityof input/output lines 52, 54, a transition region 56 and a catheter body58 that defines a plurality of individual lumens 55, 57 therein.Input/output lines 52, 54 converge and couple to catheter body 58 attransition region 56. Each input/output line 52, 54 communicates with arespective lumen 55, 57 within catheter body 58. Catheter body 58 mayalso include an expandable element 59 at a distal end thereof that hasan expanded condition and a collapsed condition. As discussed below,when the expandable element 59 is in the expanded condition, it servesas a temporary plug that seals inlet port 34 of pump body 30. Oneexample of such catheter is a Swan-Ganz® catheter (Edwards LifesciencesCorp., Irvine, Calif.).

In one embodiment, which is depicted in FIG. 2, catheter 50 may includea first input/output line or inflation line 52, which communicates withan inflation lumen 55 within catheter body 58. Additionally, catheter 50may include a second input/output line or fluid line 54, whichcommunicates with a fluid lumen 57 within catheter body 58. In addition,expandable element 59 is located at the distal end of catheter body 58and takes the form of an inflatable balloon, which when inflated,surrounds a circumference of catheter body 58. Inflation lumen 55communicates with balloon 59 such that a device, such a syringe, can beattached to inflation line 52 and deliver air or saline solution toballoon 59 via inflation lumen 55 in order to inflate balloon 59 intothe expanded or inflated condition. Conversely, the air or salinesolution can be withdrawn from balloon 59 and inflation lumen 55 todeflate balloon 59 into the collapsed or deflated condition. In theinflated condition, balloon 59 may seal inlet port 34 of pump 30, and inthe deflated condition, catheter body 58 may be removed from pump 30 andchannel 42 of pedestal 40.

Fluid lumen 57 communicates with an opening (not shown) at the distalend of catheter body 58. Such opening is preferably located beyond ordistal to balloon 59. A device, such as a syringe, can be attached tofluid line 54 so that air and/or blood that is disposed beyond or distalto balloon 59 can be drawn through fluid lumen 57. For example, whenballoon 59 is in an inflated condition and seals inlet port 34 of thepump, fluid lumen 57 can be used to de-air and prime pump 12.

Other lumens and corresponding individual lines for performingadditional functions are also contemplated. For example, a thirdinput/output line or sensor line (not shown) in communication with asensor lumen within catheter body 58 may house a wire communicating witha pressure transducer disposed within fluid lumen 57 or on an exteriorof catheter body 58 at a location distal to the temporary plug formed byexpanded balloon 59. Such sensor line and corresponding lumen can becoupled to a processor that is capable of converting signals receivedfrom the pressure transducer into pressure measurements of a fluiddisposed within fluid lumen 57. Alternatively, in one embodiment, thesensor lumen may communicate with another opening located at the distalend of catheter body 58 and sealed by a diaphragm. Deflection of thediaphragm can be measured to determine pressure of a fluid disposed atthe distal end of catheter body 58. In a further embodiment, fluid line54, or another fluid line, can be coupled to a pressure transducer,which may be located outside of the patient's body during implantation.In such embodiment, the externally situated pressure transducer canmeasure pressure at a distal opening of the catheter by sensing pressureof a fluid disposed within fluid lumen 57 and fluid line 54. Other knownconfigurations used to measure physical conditions via a catheter arealso contemplated.

In an alternative embodiment (not shown) of catheter 50, first line 52and first lumen 55 may house a wire coupled to a distal tip of thecatheter body 58. A sidewall of catheter body 58 at the distal endthereof may be configured to buckle and expand outwardly in the shape ofdisc upon the tensioning of the wire at the proximal end of catheter 50.Such configuration may be an alternative expandable element to aninflatable balloon.

FIGS. 3-7 depict an exemplary method of implanting pump 12 into a heartvia kit 10. Such method generally includes gaining access to the apex ofthe heart, attaching a mounting ring 80 to the apex, coring the leftventricular wall through mounting ring 80, partially inserting pump 12into the left ventricle, de-airing pump 12 via catheter 50, continuinginsertion of pump 12 into the left ventricle, measuring pressure sensedby catheter 50, determining when the pressure measurements indicate thatoutflow cannula 20 is partially positioned within the ascending aorta,affixing pedestal 40 to the ventricular wall, deflating and removingcatheter 50, and plugging pedestal 40 via the removable closure 46.

More particularly, prior to implantation of pump 12 into the leftventricle, catheter 50 is assembled with the transapical VAD byinserting catheter body 58 in a proximal to distal direction throughpedestal channel 42 and resilient seal 44 such that the distal end ofcatheter body 58 extends into inlet port 34 of pump body 30. This may bedone in the operating theater or performed in the manufacturing facilityin order to pre-assemble kit 10 prior to shipment to the healthcarefacility.

A syringe, or other device, is coupled to inflation lumen 52 and air orsaline solution is delivered through inflation lumen 52 from the syringeto balloon 59, thereby expanding balloon 59 into its inflated conditionwithin inlet port 42. In the inflated condition, balloon 59 serves as atemporary plug within inlet port 34. As such, rotor 36 and outflowcannula 20 are sealed from inlet port 34. Only openings 22 of outflowcannula 20 can communicate with an environment external to pump 12.

Thereafter, or concurrently with assembly of catheter 50 with thetransapical VAD, an operator gains access to the heart preferably via aleft subcostal or left thoracotomy incision to expose the apex of theheart. A mounting ring 80, which may be provided as part of implantationkit 10 along with a coring instrument 90, is attached to the apex via apledgeted purse string suture, mattress suture, or the like (best shownin FIG. 3). Examples of suitable mounting rings, coring instruments, andmethods of using same can be found in U.S. Patent ApplicationPublication No. 2007/0167968, the disclosure of which is herebyincorporate by reference. Other examples of mounting rings, includingmounting rings that include leafleted valves, can be found in U.S.Patent Application Publication No. 2015/0112120, the disclosure of whichis hereby incorporated by reference. In addition, examples of implantinga transapical VAD through a cored opening in the left ventricle can befound in the heretofore referenced '957 publication.

A slit incision or incision in the form of a cross or X, commonlyreferred to as a “crux” incision, is made within mounting ring 80,through the ventricular wall and into the left ventricle. Coringinstrument 90 is inserted through the crux incision and ventricular walltissue is resected from the heart via coring instrument 90 to form acored opening 70 (best shown in FIGS. 4 & 5). Although, it is describedthat mounting ring 80 is applied before coring the apex of the heart, itshould be understood that other techniques in which a mounting ring isapplied after cored opening 70 is formed is also applicable.

While maintaining balloon 59 in the expanded configuration, pump 12 isadvanced at least partially into the cored opening 70 (best shown inFIG. 5). Such advancement can be performed quickly to help limit bloodloss. Also, the operator may manually block the cored opening whilemaneuvering outflow cannula 20 into the opening. Blood loss can also bemitigated by a leafleted mounting ring, such as those described in theaforementioned '120 Publication and by other implantation device,examples of which can be found in U.S. Provisional Application No.62/089,910, the disclosure of which is hereby incorporated by referencein its entirety.

Air may be trapped within pump 12 beyond or distal to inflated balloon59. This air is removed to de-air outflow cannula 20 and pump body 30via another device, such as a syringe, attached to fluid line 54 ofcatheter 50. Fluid line 54 and fluid lumen 57 communicate with a distalopening beyond or distal to inflated balloon 59. Negative pressure isapplied to fluid line 54 and fluid lumen 57 via the device which in turnapplies negative pressure to the pump distal to balloon 59. As such, theair located within pump 12 is drawn out of the pump and is replaced byblood. Blood entering into the device coupled to fluid line 54 indicatesthat pump 12 has been sufficiently de-aired. De-airing removes air thatcan be potentially dangerous to the patient and also primes pump 12 withblood so that pump 12 can operate effectively upon startup. Inflatedballoon 59 helps prevent retrograde blood flow and blood loss duringadvancement of pump 12. In addition, inflated balloon 59 helps create anenvironment within pump 12 effective to determine blood pressure at thedistal tip of outflow cannula 20.

The de-aired pump 12 is then advanced through the left ventricle. Aspump 12 is advanced through the left ventricle, blood pressure mayoptionally be sensed by a pressure transducer located within catheter 50and monitored by the operator. Although, the pressure transducer orsensing location of the pressure transducer may be located in the distalend of catheter body 58 proximal to rotor 36, the blood pressuredetected by the sensor is substantially the same as that located atdistal tip 24 of outflow cannula 20. As previously mentioned, openings22 of outflow cannula 20 are the only openings through which the insideof pump 12 communicates with the outside environment while inlet port 34is plugged by balloon 59. Thus, the blood pressure within outflowcannula 20 and pump body 30 is substantially the same as the bloodpressure located at openings 22 of distal tip 24. There may be a smalloffset between pressure sensed by the pressure transducer and pressureat distal tip 24 of outflow cannula 20. However, such offset is minimalparticularly in comparison to the differences between ventricularpressure and aortic pressure, which is significant. Thus, the operatorcan use the pressure measurements taken by the pressure transducer,particularly a measured difference between ventricular pressure andaortic pressure, to determine the location of distal tip 24 relative tothe patient's anatomy.

Thus, as illustrated by the pressure wave shown in FIG. 6, as de-airedpump 12, and in particular distal tip 24 of outflow cannula 20, isadvanced through the left ventricle, the monitored pressure may indicatewhen distal tip 24 is located in the ventricle and when it extendsthrough the aortic valve into the aorta. More specifically, a transitionof distal tip 24 from the ventricle to the aorta may be indicated by achange in the morphology of the waveform. Another indication can be achange in pressure values, which may be interpreted irrespective of theactual values outputted by the sensor. An even further indication may bea pressure value itself, rather than a change in value, which may beunderstood by the operator to be a pressure value associated with theaorta and not the ventricle, and vice versa. Also, as illustrated byFIG. 7, the operator may confirm the location of distal tip 24 viafluoroscopy. Thus, catheter 50 helps provide additional confirmation ofthe location of distal tip 24 relative to the patient's anatomy asidefrom the usual technique of fluoroscopic imaging.

Once distal tip 24 is properly located within the ascending aortabetween the aortic root and aortic arch, pedestal 40 can be attached tothe ventricular wall. This may be performed by attaching pedestal 40 tothe mounting ring 80 as is known in the art, such as by clampingpedestal 40 with mounting ring 80, for example. At this point, catheter50 preferably remains within channel 42 of pedestal 40 and, along withresilient seal 44, seals channel 42 during attachment, which helpsprevent retrograde blood loss through pedestal 40.

Once pedestal 40 is properly secured, balloon 59 of catheter 50 isdeflated or collapsed, which may be performed by withdrawing air orsaline solution therefrom. Catheter 50 is pulled proximal to pedestal 40and catheter body 58 advanced through channel 42 in a distal to proximaldirection. Catheter body 58 is withdrawn from inlet port 34 and fromchannel 42 of pedestal 40. Once catheter body 58 is advanced to aproximal location beyond resilient seal 44, resilient seal 44 closes toprovide a one-way temporary seal until channel 42 can be permanentlyplugged. Channel 42 is permanently plugged by threading or otherwisesealingly engaging the proximal end of channel 42 with closure 46 (bestshown in FIG. 8). Pump 12 may then be activated and the access incisionclosed.

FIG. 9 depicts an alternative transapical VAD implantation kit 100. Kit100 includes a VAD having a pedestal 140, pump body 130, and outflowcannula 120 similar to that of kit 10, but differs with respect to thecatheter 150. Catheter 150 includes an expandable element/balloon 159that may be cylindrical and dimensioned to tightly/sealingly fit withinthe space between pedestal 140 and pump body 130 when expanded into anexpanded condition. Thus, balloon 159, when expanded, can occlude aninlet of pump body 130 without being disposed therein. In addition, whenexpanded, balloon 159 may have a diameter as large as that of pedestal140 and/or pump body 130, and when deflated may have a diametersufficiently small to slide through a channel within pedestal 140.

Catheter 150 may include balloon 159 in addition to a distal balloon,which may be similar to that of balloon 59 described above and may beconfigured for placement within the inlet of pump body 130. In such anembodiment, catheter 150 may include a second inflation lumen to feedballoon 159 so that balloon 159 is separately expandable from the distalballoon. Alternatively, balloon 159 may be the only balloon providedwith catheter 150.

Balloon 159 helps fill the space between pedestal 140 and pump body 130,which can help reduce blood loss during implantation as it helps preventblood from flowing around pump body 130 and out of a cored opening inthe heart. In other words, as pump body 130 is inserted through a coredopening in the heart, pump body 130 may at least partially occlude thecored opening. However, once pump body 130 is fully inserted into theventricle but prior to pedestal 140 being placed within the coredopening, blood may flow around pump body 130 into the space betweenpedestal 140 and pump body 130 and out of the cored opening. Balloon 159fills this space and helps occlude the cored opening until pedestal 140is inserted therein.

EXAMPLE

Transapical ventricular assist devices were implanted in healthy bovine(n=4) via a thoracotomy without use of CPB. A Swan-Ganz balloon catheterwas inserted into an access channel inside the pedestal and advancedinto the pump inflow. A mounting ring was attached at the LV apex andthe pump was inserted after coring to form a hole in the wall of theheart. Once the pump was fully inserted through the mounting ring andthrough the hole in the heart-wall formed by coring, the mounting ringwas mechanically engaged with the pedestal so as to hold the pump inplace. In this condition, the pedestal and sealing ring closed the holein the heart wall. The balloon was inflated during pump insertion toprevent retrograde flow through the pump. The fluid lumen of thecatheter was used to de-air the pump and was connected to a fluidpressure line and thus to a pressure measuring instrument. Pressurewaveforms were monitored during insertion to verify positioning in LVand across the aortic valve. After pump insertion, the balloon wasdeflated and the catheter was retracted so as to remove the balloon andcatheter from the heart through the channel in the pedestal. Theproximal end of the channel disposed outside the heart was sealed with aclosure in the form of a plug threadedly engaged in the channel.

Results

Average implant time of 5 minutes from LV coring to pump start with lessthan 50 mL of blood loss was achieved. Swan-Ganz balloon inflationsuccessfully prevented backflow of blood through the pump duringinsertion. Fluoroscopic images confirmed cannula placement across theaortic valve and pump alignment along the LV outflow tract.

Although the above methods and techniques are described in relation tothe implantation of pump 12 into the left ventricle, it should beunderstood that pump 12 can be implanted into the right ventricle withoutflow cannula 20 extending into the pulmonary artery. In addition, itshould be understood that catheter 50 can be used in conjunction withother pumps and other delivery approaches without departing from theprinciples described herein.

Also, while the invention herein has been described with reference toparticular embodiments, it is to be understood that these embodimentsare merely illustrative of the principles and applications of thepresent invention. It is therefore to be understood that numerousmodifications may be made to the illustrative embodiments and that otherarrangements may be devised without departing from the spirit and scopeof the present invention as defined by the appended claims.

What is claimed is:
 1. A pump installation kit, comprising: a pumpincluding a pump body having an interior and an inlet communicating withthe interior, a pumping element mounted within the interior, and anoutlet cannula communicating with the interior of the pump body, thepump being adapted for mounting with the pump body and inlet disposedwithin a ventricle of a heart; and a temporary plug adapted forreleasable, sealing engagement in the inlet.
 2. The kit of claim 1,further comprising a securement ring adapted for mounting to the outsideof the heart, and a pedestal being adapted for mounting to thesecurement ring and being mechanically coupled to the pump, the pedestalhaving a channel having proximal and distal ends, the distal end of thechannel communicating with the ventricle and the proximal end of thechannel being disposed outside of the heart when the pedestal is mountedto the securement ring.
 3. The kit of claim 2, further comprising anelongated element mechanically connected to the temporary plug, theelongated element extending through the channel when the temporary plugis engaged in the inlet, the temporary plug being adapted to pass out ofthe heart through the channel after the temporary plug is disengagedfrom the inlet port.
 4. The kit of claim 3, wherein the temporary plughas an expanded condition and a collapsed condition, and the temporaryplug is adapted to pass out through the channel in the collapsedcondition.
 5. The kit of claim 3, wherein the elongated element is acatheter having an inflation lumen and the temporary plug includes aballoon communicating with the inflation lumen.
 6. The kit of claim 3,wherein the elongated element is a catheter having a fluid lumen, thefluid lumen communicating with the interior of the pump when thetemporary plug is engaged in the inlet port.
 7. The kit of claim 6,further comprising a pressure measuring instrument connectable to thefluid lumen.
 8. The kit of claim 6, further comprising a closure adaptedto seal the channel in the pedestal.
 9. The kit of claim 8, wherein theclosure includes a screw adapted to threadedly engage the channel. 10.The kit of claim 3, further comprising a resilient seal disposed withinthe channel, the resilient seal sealingly engaging the elongated elementand the pedestal when the elongated element is disposed within thechannel.
 11. The kit of claim 10, wherein the resilient seal is aone-way valve adapted to prevent blood flow from the proximal end of thechannel when the elongated element is removed therefrom.